Capnograph system further detecting spontaneous patient breaths

ABSTRACT

A capnograph system may be used together with a ventilation system for a patient. The capnograph system may include a capnography module with a carbon dioxide detector, which may generate a carbon dioxide signal responsive to an amount of carbon dioxide detected within an air path of the ventilation system. A monitoring circuit may further detect a pressure within the air path. A processing component within the capnography module may generate a pressure signal responsive to the pressure detected in the air path. The pressure signal, alone or in combination with other signals such as the carbon dioxide signal, may be used to detect spontaneous breaths of the patient.

CROSS REFERENCE TO RELATED PATENT APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/836,658, filed on Dec. 8, 2017, which claims priority from U.S.Provisional Patent Application Ser. No. 62/432,535, filed on Dec. 9,2016.

BACKGROUND

Cardio Pulmonary Resuscitation (CPR) includes chest compressions andventilations. Ventilations are artificial breaths that a rescuer, suchas a paramedic, may inject into a patient's lungs, whether by using aventilator system for administering breaths mechanically andartificially or not.

Some ventilator systems include an airway tube that is inserted into thepatient's airway. Such an airway tube can be an endotracheal (ET) tubeor a supraglottic airway laryngopharyngeal tube. The airway tube can beinserted from an airway opening of the patient, which may be the mouth,the nostrils, a small incision in the trachea, etc. The insertion is aprocess that is known as intubation, and is often performed according toa process called Rapid Sequence Intubation (RSI). When intubation isthus complete, the artificial breaths can be delivered at a certainappropriate and prescribed rate.

A patient might have a reflexive reaction against the intubation. Toprevent that, a rescuer may first need to administer sedation and/or aparalytic drug, and then wait for it to take effect. In the event thatthe patient is unconscious, for example from a cardiac arrest, the drugsmay not be needed. Still, a patient in cardiac arrest can be intubatedduring arrest or shortly after return of spontaneous ventilation, andventilation at the certain prescribed rate is still needed in thosepatients.

Problems may arise when the sedation and/or the paralytic drug startwearing off. It can be worse when both have been administered, and theystart wearing off at different times. A patient may attempt one or morespontaneous breaths, which can be a good indication that mechanicalventilation is no longer necessary, or that the breaths beingadministered mechanically do not provide enough ventilation.

All subject matter discussed in this Background section of this documentis not necessarily prior art, and may not be presumed to be prior artsimply because it is presented in this Background section. Plus, anyreference to any prior art in this description is not, and should not betaken as, an acknowledgement or any form of suggestion that such priorart forms parts of the common general knowledge in any art in anycountry. Along these lines, any recognition of problems in the prior artdiscussed in this Background section or associated with such subjectmatter should not be treated as prior art, unless expressly stated to beprior art. Rather, the discussion of any subject matter in thisBackground section should be treated as part of the approach takentowards the particular problem by the inventor. This approach in and ofitself may also be inventive.

BRIEF SUMMARY

The present description gives instances of medical devices, systems,components, and methods, the use of which may help overcome problems andlimitations of the prior art. In embodiments, ventilation systems may beused for patients, and spontaneous breaths of patients may be detectedthat have cardiac arrest, had cardiac arrest, or for any reason had beenintubated with an endotracheal tube to protect their airway and/orenable mechanical ventilation.

In embodiments, a capnograph system may be used together with aventilation system for a patient. The capnograph system may include acapnography module with a carbon dioxide detector, which may generate acarbon dioxide signal responsive to an amount of carbon dioxide detectedwithin an air path of the ventilation system. A monitoring circuit mayfurther detect a pressure within the air path. A processing componentwithin the capnography module may generate a pressure signal responsiveto the pressure detected in the air path. The pressure signal, alone orin combination with other signals such as the carbon dioxide signal, maybe used to detect spontaneous breaths of the patient.

In embodiments, a monitor system may detect spontaneous breaths by apatient. In particular, the monitor system may be used together with aventilation system that includes an airway adapter. In some embodiments,the monitor system includes a defibrillator module, in which case it isa monitor-defibrillator. The monitor system may include a capnographymodule with a carbon dioxide detector, which may generate a carbondioxide signal responsive to an amount of carbon dioxide detected withinan air path of the ventilation system. The capnography module may alsoinclude a pressure detector to detect a pressure within the air path,and a processing component to generate a pressure signal from thedetected pressure. A processor may detect a spontaneous breath of thepatient from an aspect of the pressure signal, and possibly also from anaspect of the carbon dioxide signal.

In embodiments, a capnograph airway adapter for a ventilator has a sidetube adapted to further detect spontaneous patient breaths. Inparticular, the capnograph airway adapter can be configured to be usedtogether with a ventilation system that includes a gas source and anairway tube. The capnograph airway adapter may include an airway adapterconfigured to be coupled between the gas source and the airway tube, anda side tube configured to be coupled with the capnograph airway adapter.A strain is gauge coupled to the side tube, and is configured to becoupled with a bridge circuit for generating a pressure signal about apressure in the side tube.

In embodiments, a capnograph airway adapter for a ventilator is adaptedto further detect spontaneous patient breaths. In particular, thecapnograph airway adapter can be configured to be used together with aventilation system that includes a gas source and an airway tube. Thecapnograph airway adapter may include an airway adapter configured to becoupled between the gas source and the airway tube. A strain gauge canbe coupled to the airway adapter, and be configured to be coupled with abridge circuit for generating a pressure signal about a pressure in theairway adapter.

In embodiments, an impedance threshold device (ITD) is adapted to helpdetect spontaneous patient breaths. In particular, the impedancethreshold device can be used together with a ventilation system thatincludes a gas source and an airway tube. The impedance threshold deviceincludes a tube section that can be coupled between the gas source andthe airway tube, and an inflow valve within the tube section. The inflowvalve can be closed so as to block the air path until a negative airwaypressure threshold is exceeded, at which time the closed inflow valvecan open so as to unblock the blocked air path. A strain gauge iscoupled to the tube section, and is configured to be coupled with abridge circuit for generating a pressure signal about a pressure in thetube section.

In embodiments, an impedance threshold device (ITD) is adapted to helpdetect patient carbon dioxide. In particular, the impedance thresholddevice can be used together with and a capnography module and aventilation system that includes a gas source and an airway tube. Theimpedance threshold device includes a tube section that can be coupledbetween the gas source and the airway tube, and a side tube configuredto be coupled to the capnography module. An inflow valve within the tubesection can be closed so as to block the air path until a negativeairway pressure threshold is exceeded, at which time the closed inflowvalve can open so as to unblock the blocked air path.

In embodiments, a ventilator endotracheal tube has a strain gauge forhelping detect spontaneous patient breaths. In particular, anendotracheal (ET) system for a ventilator includes an ET tube, and astrain gauge coupled to the ET tube. A bridge circuit can be configuredto be coupled with the strain gauge so as to detect pressure changeswithin the ET tube.

An advantage can be that the detected spontaneous breaths can becommunicated to rescuers, who can adjust accordingly what they do. Insome embodiments, spontaneous breaths can be detected without having asensor in an air path, and inexpensively in many embodiments. Inaddition, the performance of a rescue team can be assessed moreaccurately. For example, spontaneous breaths will not surreptitiouslyblemish the record of a team member who has been ventilating at a properpace.

Moreover, the detected spontaneous breaths can become part of theoverall resuscitation record. Presence or absence of patient-initiatedbreaths can give clues about respiratory drive of patients, which isrelated to adequacy of ventilation. It can also give clues about thestatus of paralytic drugs administered as part of Rapid SequenceIntubation (RSI). That is, documentation can be created as to when aparalytic drug has worn off.

These and other features and advantages of the claimed invention willbecome more readily apparent in view of the embodiments described andillustrated in this specification, namely from this writtenspecification and the associated drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram of sample components of a capnograph system and of aventilation system made according to embodiments.

FIG. 2 illustrates a sample comparison of sample time diagrams ofwaveforms of signals of FIG. 1, for detecting spontaneous patientbreaths according to embodiments.

FIG. 3 is a diagram showing sample components of a monitor system thatmay include a capnography module of FIG. 1, according to embodiments.

FIG. 4 is a diagram of a sample embodiment of a capnography module ofFIG. 1.

FIG. 5 is a diagram of another sample embodiment of a capnography moduleof FIG. 1.

FIG. 6 is a diagram of sample embodiments of an airway adapter usedtogether with an embodiment of a capnography module.

FIG. 7 is a diagram of sample embodiments of an airway adapter usedtogether with a side tube with a strain gauge and a capnography module.

FIG. 8 is a diagram of sample embodiments of an airway adapter usedtogether with a strain gauge and a capnography module.

FIG. 9 is a section diagram of a component that can accommodate a straingauge by having portions of different elasticities according toembodiments.

FIG. 10 is a section diagram of a component that accommodates a straingauge on portions of different elasticities according to embodiments.

FIG. 11 is a section diagram of a component that can accommodate astrain gauge by having portions of different thicknesses according toembodiments.

FIG. 12 is a section diagram of a component that accommodates a straingauge on portions of different thicknesses according to embodiments.

FIG. 13 is a flowchart for illustrating methods according toembodiments.

FIG. 14 is a diagram of a sample combination airway adapter withimpedance threshold device, made according to embodiments.

FIG. 15 is a diagram of components of a sample endotracheal (ET) systemmade according to embodiments, shown inserted in a patient's airway.

DETAILED DESCRIPTION

As has been mentioned, the present description is about medical devices,systems, components and methods. Embodiments are now described in moredetail.

FIG. 1 shows a portion of a patient 111, with an airway opening 114 andone of their lungs indicated as 118. A capnograph system 100 accordingto embodiments is shown, which is configured to be used together with aventilation system 101 according to embodiments. In some embodiments,the components of system 100 and system 101 may overlap, for bettercooperation.

Ventilation system 101 includes a gas source 120. The gas of source 120can be oxygen, air, a mixture thereof, other combinations of gases, etc.Gas source 120 can be configured to expel repeated bursts of the gasthrough a gas source tube 121. For expelling, gas source 120 may bemechanized or manual. In some manual embodiments, gas source 120includes a bag that can be squeezed by a rescuer, each squeezingdelivering one of the bursts.

Ventilation system 101 may have additional components, which are notshown so as not to clutter FIG. 1. For example, a 1-way valve can beadded some place after gas source 120. Such a 1-way valve performs twofunctions. First, when an artificial breath is administered, it allowsgas from gas source 120 to pass into air path 149, and from thereeventually to lung 118 of patient 111. Second, when patient 111 exhales,in other words, expires, the 1-way valve blocks the expired gases fromreaching back to gas source 120; rather, the 1-way valve redirects theseexpired gases to be exhausted in the environment, or another tubeinstead.

A ventilation system according to embodiments includes and/or isconfigured to work with an airway tube. Examples of airway tubes includean endotracheal (ET) tubes, supraglottic airway laryngopharyngeal tubes,etc. In this description often an ET tube is shown, but that is by wayof example and not of limitation, plus aspects of its description forpurposes of this document may apply also to other types of airway tubes.

Ventilation system 101 also includes an endotracheal (ET) tube 140, ofwhich two portions are shown in different scales, and connected by threedots. In particular, patient 111 is intubated by ET tube 140, and afirst portion of ET tube 140 has been inserted through airway opening114 into the trachea of patient 111. As such, a first end 141 of ET tube114 is thus brought close to lung 118. A second portion of ET tube 140is also shown, having a second end 142.

ET tube 140 defines an air path 149 that communicates with gas sourcetube 121 and gas source 120. As such, when ET tube 140 is thus insertedin the patient's airway, it can be configured so as to guide the bursts124 of gas as artificial inhalations to lung 118 of patient 111. Gasexpulsion by source 120 results in a pressure difference between theinterior of ET tube 140 and the atmosphere, slightly stretching ET tube140. The pressure in the interior of ET tube 140 is referred to as thepatient's airway pressure and is also closely related to the patient'sintrathoracic pressure.

Additional components may be coupled between ET tube 140 and gas source120, in a manner that preserves and accommodates air path 149. Suchcomponents may include adapters, fittings, valves, etc. Coupling canhappen because the components are usually tubular, and circular, andemploy a male-female matching configuration.

In the example of FIG. 1 such a component is an airway adapter 150,which is configured to be coupled between gas source 120 and ET tube140. Airway adapter 150 has a first end 151 that is coupled to secondend 142 of ET tube 140. Airway adapter 150 also has a second end 152that is coupled to gas source tube 121. Airway adapter 150 has a hollowinterior, so as to accommodate air path 149 when it is thus coupled.

Capnograph system 100 can be configured to detect carbon dioxide inexhalations of patient 111, and also a pressure in air path 149.Capnograph system 100 may include a capnography module 160 that has acarbon dioxide detector 168. Carbon dioxide detector 168 can beconfigured to generate a carbon dioxide signal S169 responsive to anamount of carbon dioxide detected within air path 149 of ventilationsystem 101.

Capnograph system 100 may also include a monitoring circuit 170 that isdistinct from carbon dioxide detector 168. Monitoring circuit 170 can beconfigured to detect a pressure in air path 149. Monitoring circuit 170may have a processing component 172 within capnography module 160, anddistinct from carbon dioxide detector 168. In fact, in some embodiments,monitoring circuit 170 is wholly included within capnography module 160,while in other embodiments not necessarily. Processing component 172 canbe configured to generate a pressure signal S179 responsive to thepressure detected in air path 149 by the monitoring circuit 170. Asexplained later in this document, pressure signal S179, alone or incombination with other signals such as carbon dioxide signal S169, maybe used to detect spontaneous breaths of the patient.

In embodiments, capnography module 160 communicates with air path 149 bymeans of a side tube 162, which can be configured to be coupled betweenairway adapter 150 and capnography module 160. In fact, airway adapter150 may be interposed in air path 149 for the purpose of providing theopportunity of side tube 162 to access air path 149, for sampling thegases and the pressure therein. The gases include a mixture of gasesexpelled by source 120 as bursts, and also from patient 111 asexhalations. For operation, side tube 162 may be passed through anopening 163 in a housing 109 of capnography module 160, or of a monitorthat houses capnography module 160, a monitor-defibrillator system, etc.In such configurations, capnography module 160 can be characterized as aside stream capnograph.

In some embodiments, capnography module 160 includes a cuvette 164,which is a small chamber. Side tube 162 can be coupled to cuvette 164.Capnography module 160 may also include a pump 165, which is configuredto draw gas from air path 149 into cuvette 164. This way, gases in airpath 149 can be sampled while in cuvette 164. After that, the sampledgases can be disposed of via an exhaust tube 166. It will be understoodthat pump 165 withdraws, for sampling the vertical column of air path149, relatively little gas compared to what is needed for ventilatingthe patient. In addition, as long as pump 165 withdraws gas at aconstant rate, that will not mask the transient nature of a peak that isintended to be detected.

In such embodiments, a light source 167 in capnography module 160 mayilluminate the interior of cuvette 164, and carbon dioxide detector 168detects an amount of the carbon dioxide within cuvette 164, by measuringhow much light from source 167 reaches it. In some embodiments, lightsource 167 emits infrared (IR) light.

As mentioned above, pressure signal S179, alone or in combination withother signals such as carbon dioxide signal S169, may be used by aprocessor to detect spontaneous breaths of the patient according toembodiments. Examples are now described.

FIG. 2 illustrates a sample comparison of sample time diagrams ofwaveforms W269, W279. Waveforms W269, W279 can be those of signals S169,S179 respectively. Aspects of waveforms W269, W279 are a baseline value,and peaks away from the baseline value. The baseline value can be set tozero, or be thought of as zero. The peaks are transient, in the sensethat the waveforms return to the baseline value.

Waveform W269 indicates an amount of carbon dioxide. Strictly speaking,it is a measure of the partial pressure of carbon dioxide, of amount ofcarbon dioxide in cuvette 164, and so on.

Waveform W269 has peaks 263, 264, 265, 266, 267, which correspond toexhalations. These exhalations can be from both the artificial breathsand any spontaneous breaths.

Waveform W279 indicates pressure changes within air path 149, from abaseline. As will be appreciated, in cases where an ET tube forms anairtight seal, at a first approximation the pressure within air path 149is uniform within air path 149, and even within side tube 162 andcuvette 164. This uniform pressure is shown as the baseline zero, eventhough it may have a non-zero value. It can be thought of as thedifference between pressure in the airway and pressure in the ambientatmosphere surrounding the airway tube. At a second approximation, therecan be pressure waves in advance of a new pressure being established,plus pump 165 may introduce a boundary condition of reducing pressure.Notwithstanding the effect of pump 165, pressures changes from thebaseline within air path 149, i.e. changes from artificial breaths andfrom any spontaneous breaths, can result in corresponding pressurechanges being established within side tube 162 and within cuvette 164.

Waveform W279 has positive peaks 273, 274, 277, plus negative peaks 275,276 that are discussed later. Positive peaks 273, 274, 277 amount togusts or bursts by gas source, in other words, artificial inhalationsfor the patient.

For detecting spontaneous breaths by the patient, waveform W289 is madefirst by repeating waveform W269, and then by removing from thatwaveform peaks that can be attributed to peaks of waveform W279. Inother words, waveform W289 first is made with peaks 283, 284, 285, 286,287, which repeat peaks respective 263, 264, 265, 266, 267 of waveformW269. But then, peaks 283, 284, 287 are removed from waveform W289,because their presence is explained, attributed to peaks 273, 274, 277as artificial inhalations. Accordingly, waveform W289 is left only withpeaks 285, 286, from peaks 265, 266, which can be deduced to bespontaneous breaths.

The description above used only positive pressure in waveform W279. Thatwould be applicable, for example, if only increases of the pressure inthe airway were detectable. In some embodiments, negative pressurechanges can also be detected, which would result in peaks 275, 276.Negative pressure changes are sometimes called “negative pressure”.Similarly, where pressure detectors are provided in this disclosure todetect pressure, it is often the change in pressure that is of interestfor signal S169 to convey. In such embodiments, waveform W279 ofpressure signal S179 alone can be used for detecting the presence ofspontaneous breaths, since spontaneous breaths result in negativepressure changes. As such, in those embodiments a comparison with carbondioxide waveform W269 may not be necessary, but used nevertheless toconfirm the presence of corresponding exhalation peaks 265, 266, and soon. Of course, negative pressure peaks of much magnitude may beuncommon, except when an ITD is being used and a spontaneous inspirationis initiated.

A person skilled in the art will recognize that a simplification hasbeen made in FIG. 2, for explaining more easily the correspondence, andattribution, of peaks in waveforms W269 and W279. The simplification isthat corresponding peaks are shown as occurring at the same time. Thismight indeed be the case if all the sensing were happening at the samelocation within the vertical column of air path 149. Where, however,signal S169 is derived by a detection of gas withdrawn after side tube162, waveform W269 may appear with a concomitant first time delayrelative to FIG. 2. And, if the pressure is detected within the columnof air path 149, waveform W279 may appear with no time delay. Or, if thepressure is detected on side tube 162 or in module 160, waveform W279may appear with a concomitant second time delay relative to FIG. 2. Thepotentially first time delay may be different from the second timedelay. For attribution of the peaks, the potentially different timedelays can be corrected by a processor, whether in in real time, or bybeing known in advance. Knowing in advance can be by the factory, by acalibration process, and so on. For detection, detection windows may beestablished for confirming a peak is established or not. In addition,detection windows may be set to prevent negative peak detection, and soon.

Of course, in matching and interpreting aspects such as peaks fordetecting spontaneous breaths, a person skilled in the art may useadditional features. For example, a trailing edge of the CO₂ peaks inwaveform W269 may occur when a fresh burst of gas enters the air pathfrom the gas source, or even ambient air if permitted. If the airwaypressure is positive at the time the CO₂ level drops to zero, this canbe detected as an administered artificial breath; if, however, theairway pressure is not positive at the time the CO₂ level drops to zero,the breath must be a spontaneous breath drawn in by the patient.Moreover, the person skilled in the art will adjust for the impact of a1-way valve; even where present, this impact may not be much, as itstime constant may be slower than what is being detected.

Referring now to FIG. 3, in some embodiments, a monitor system 300 maydetect spontaneous breaths by a patient. In particular, monitor system300 may be used together with a ventilation system that includes anairway adapter, as seen in FIG. 1. Of course, embodiments of FIG. 1 canbe implemented with or without monitor system 300. In other words,monitor 300 is optional, in the sense that what is described for usingthe pressure signal S179 may also take place within an overall monitor300.

In some embodiments, monitor system 300 is provided in a housing 309.Monitor system 300 may include a defibrillator module 333, in which casesystem 300 is a monitor-defibrillator. Monitor system 300 may include acapnography module 360, which can be as described elsewhere in thisdocument, and generate a carbon dioxide signal S369 similar to S169.Capnography module 360 may include a pressure detector (not shown inFIG. 3), to detect a pressure within the air path of the ventilationsystem.

In general, a monitoring circuit 370 may detect a pressure within theair path. Monitoring circuit 370 may include a processing component 372similarly to what is described elsewhere in this document. Processingcomponent 372 may generate a pressure signal S379 responsive to thepressure detected in the air path. In the embodiment of FIG. 3,monitoring circuit 370 is completely part of capnography module 360.

Monitor system 300 also includes a processor 390, which can be coupledto receive pressure signal S379, and optionally also carbon dioxidesignal S369. Processor 390 may optionally be part of capnography module360. Either way, processor 390 may detect a spontaneous breath of thepatient from an aspect of pressure signal S379, and possibly also froman aspect of carbon dioxide signal S369. As also explained withreference to FIG. 2, processor 390 can be configured to detect thespontaneous breath from aspects, such as peaks, of pressure signal S379and of carbon dioxide signal S369. In fact, detection can be frommismatched aspects of these signals.

As further explained with reference to FIG. 2, processor 390 can beconfigured to detect spontaneous breaths from an aspect of pressuresignal S379 that indicates negative pressure. Such aspect can benegative changes in a baseline pressure signal, for example negativepeaks 275, 276. In some embodiments, processor 390 is configured toconfirm the detected spontaneous breath from an aspect of carbon dioxidesignal S369, for example as described above for peaks 265, 266.

A capnograph system according to embodiments, and/or monitor system 300,may further include an output device 314. If monitor system 300 isindeed provided, output device 314 can be part of a user interface 310of monitor 300. Output device 314 can be configured to output ahuman-perceptible indication, such as a sound, a light, a screenindication and the like, responsive to processor 390 receiving pressuresignal S379. As such, output device 314 can include a light, a screen, aspeaker, and so on. The human-perceptible indication can be thatspontaneous breaths are indicated, and that the rescue team shouldconsider reacting to them. Additional human-perceptible indicationscould be provided for additional events, for example responsive to themechanical breaths. Such can be useful guidance to the person takingcare of the patient. Moreover, items mentioned below for reporting mayalso be shown on a screen, such as reporting the number (or rate) ofspontaneous and positive pressure breaths, and so on.

A capnograph system according to embodiments, and/or monitor system 300,may further include a memory 388. Memory 388 may optionally be part ofcapnography module 360. Memory 388 can be configured to store a record389, responsive to processor 390 receiving pressure signal S379. Assuch, record 389 can indicate spontaneous breaths, of the type detectedat waveform W289 of FIG. 2.

After an event, a report 318 can be generated. Report 318 may include,along with other events, a record 319 of spontaneous breaths that can bederived from record 389. Such other events may include efforts of therescue team, shocks delivered by defibrillator module 333, and otherdata captured by monitoring circuit 370. There can be reportingseparately the number (or rate) of spontaneous and positive pressurebreaths, carbon dioxide (CO₂) levels (end tidal or maximum) separatelyfor the spontaneous and positive pressure breaths. This might be usefulin the future, while it is a good idea to have some real data gatheredby such a system, to better define how a clinician should use those twodifferent CO₂ levels.

Report 318 may further include data entered by the rescue team, forexample what sedation and/or paralytic drugs were delivered and when.Such entries can be made by an input device 312 of user interface 310.As such, input device 312 can include a touchscreen, other hapticdevice, a keyboard, keypad, custom buttons, etc. Moreover, report 318may include statistics extracted from the performance of the rescueteam, for example a Figure of Merit about artificially deliveredbreaths, about reacting to the detected spontaneous breaths, etc.

Sample embodiments of capnograph systems are now described, for howmonitoring circuit 170 of FIG. 1 can be implemented.

Referring now to FIG. 4, in an embodiment 460, a cuvette 464 has gasdrawn into it by a pump 465. A carbon dioxide detector 468, assisted bya light source 467, generates a carbon dioxide signal S469, allsimilarly to what was described above. In embodiment 460, the previouslymentioned monitoring circuit includes a pressure sensor 470. Pressuresensor 470 can be configured to detect a pressure of the gas withincuvette 464, for example by being within cuvette 464. In other words,the pressure within the air path is detected by detecting pressurewithin cuvette 464.

For another example, referring now to FIG. 5, in an embodiment 560, acuvette 564 has gas drawn into it by a pump 565. A carbon dioxidedetector 568, assisted by a light source 567, generates a carbon dioxidesignal S569, all similarly to what was described above. In embodiment560, pump 565 includes at least one power node 561. Pump 565 can beconfigured to receive a pump driving signal at power node 561, and tooperate as described above responsive to the pump driving signal. Thepump driving signal can be electrical of course, and one or moreconductors 562 may deliver the pump driving signal to power node 561.

In embodiment 560, the previously mentioned monitoring circuit mayinclude a driving sensor 570 configured to detect changes in the pumpdriving signal. These changes in the pump driving signal can be because,when there are positive pressure events of artificial inhalations, pump565 will need to work momentarily less hard to maintain the same rate ofoperation, and therefore momentarily draw less current. Plus, when thereare negative pressure events of spontaneous breaths, pump 565 will needto work momentarily harder to maintain the same rate of operation, andtherefore momentarily draw more current. As such, driving sensor 570 canbe configured to detect voltage at power node 561, or current at one ormore conductors 562, and so on.

Referring now to FIG. 6, in an embodiment 610, an airway adapter 650 hasa hollow interior 658 for accommodating an air path 649. Airway adapter650 can communicate with a capnography module 660 via a side tube 662.Capnography module 660 includes a cuvette 664. Moreover, a carbondioxide detector 668 can generate a carbon dioxide signal S669 about agas in cuvette 464, all similarly to what was described above. Inaddition, capnography module 660 includes a processing component 672.

In embodiment 610, the previously mentioned monitoring circuit includesa pressure detector 670. Pressure detector 670 can be coupled to airwayadapter 650, and configured to detect a pressure in hollow interior 658.Pressure detector 670 can be configured to generate a pressure detectionsignal responsive to the pressure detected in hollow interior 658.Moreover, the monitoring circuit may further include an antenna 675.Antenna 675 can be configured to transmit wirelessly the pressuredetection signal.

In embodiment 610, capnography module 660 also includes a wirelesscommunication module (WCM) 678. WCM 678 can be configured to receive thewirelessly transmitted pressure detection signal, for example over acommunication link 676. This wireless communication link 676 can beimplemented in a number of ways. For example, antenna 675 can be theantenna of a Radio Frequency Identification (RFID) tag on which valuesof the pressure detection signal are written, and WCM 678 can include anRFID reader that queries the RFID tag frequently enough to detectchanges.

A related suitable device is Pressure and Temperature Sensor,Ultra-Miniature, High-Temperature, Low Frequency (134 KHz) RFID PassiveWireless Sensor which, at the time this document was initially filedwith the US Patent Office, was offered by PHASE IV ENGINEERING, INC.,2820 Wilderness Place Unit C, Boulder, Colo. 80301.

WCM 678 can be further configured to convey an interim signal toprocessing component 672, responsive to the received pressure detectionsignal. In embodiment 610, processing component 672 can be configured togenerate a pressure signal S679 responsive to the received interimsignal.

In some embodiments an inflow valve is further provided within theinterior of the airway adapter, for increasing the duration andmagnitude of negative airway pressures. This type of inflow valve isalso known as CPR inflow valve and impedance threshold device (ITD) andcan be made, for example, as described in U.S. Pat. No. 5,692,498. Sucha CPR inflow valve may promote venous blood flow into the heart andlungs from the peripheral venous vasculature, especially during CPR. Itshould be noted, however that, where such an inflow valve is provided,perhaps care should be taken to account for a strain gauge being alsoused, and being subjected to negative air path pressure. In particular,if a patient initially tries to take a breath against resistance of theinflow valve, a tube section or adapter may contract. This should beconsidered in terms of the scenario, in particular whether the patientwill be expected to be taking breaths voluntarily, etc.

For example, in embodiment 610 an inflow valve 688 is optionallyprovided within interior 658 of airway adapter 650. Inflow valve 688 canbe configured to be closed so as to block air path 649 and thus preventthe bursts of gas from entering the lungs until a negative airwaypressure threshold is met or exceeded. This negative airway pressurethreshold can be set by how the valve is made, or be adjustable, in thefield or by a medical director. At the time that the threshold is met orexceeded, the then-closed inflow valve 688 can be configured to open, soas to unblock the then-blocked air path 649.

These embodiments of FIG. 6 contemplate putting components within airpath 649. Over time, matter may accumulate onto such components, whichcan create problems such as varying the measurements and even getting inthe way of effective ventilation. As such, cleaning and maintenance maybe needed.

There is a number of ways to detect pressure within the air path and,more particularly, changes in that pressure, according to embodiments.Since transients are of interest, measurement need not be very accurateand the pressure signal need not be high fidelity. For example, sensorscould include capacitive sensing of the presence of positive airwaypressure. Additional examples are now described.

In some embodiments, the previously mentioned monitoring circuitincludes a strain gauge, and a bridge circuit configured to be coupledelectrically with the strain gauge. The strain gauge may indicate whenan elastic component changes size due to pressure inside it; forexample, a component's circumferential size may become larger if thereis a positive pressure change from the baseline, or smaller if there isa negative pressure from the baseline. The bridge circuit can be used todetect a change in the electrical resistance of the strain gauge. Thebridge circuit may or may not be within the capnography module. Thebridge circuit may or may not part of the previously mentionedprocessing component. Examples are now described.

Referring now to FIG. 7, in an embodiment 710, an airway adapter 750 hasa hollow interior 758 for accommodating an air path 749. A CPR inflowvalve 788 can optionally be provided within interior 758 of airwayadapter 750. Airway adapter 750 can communicate with a capnographymodule 760 via a side tube 762. Capnography module 760 includes acuvette 764. Moreover, a carbon dioxide detector 768 can generate acarbon dioxide signal S769 about a gas in cuvette 764, all similarly towhat was described above. In addition, capnography module 760 includes aprocessing component 772.

In embodiment 710, the previously mentioned monitoring circuit includesa strain gauge 770. Strain gauge 770 is attached to side tube 762. Inaddition, processing component 772 includes a resistor bridge 773.Resistor bridge 773 is made of resistors R1, R2, R3 as shown, and isconfigured to be coupled with strain gauge 770 via wires 771. Inembodiment 710, processing component 772 can be configured to generate apressure signal S779 responsive to signals on resistor bridge 773.

For another example, referring now to FIG. 8, in an embodiment 810 anairway adapter 850 has a hollow interior 858 for accommodating an airpath 849. A CPR inflow valve 888 can optionally be provided withininterior 858 of airway adapter 850. Airway adapter 850 can communicatewith a capnography module 860 via a side tube 862. Capnography module860 includes a cuvette 864. Moreover, a carbon dioxide detector 868 cangenerate a carbon dioxide signal S869 about a gas in cuvette 864, allsimilarly to what was described above. In addition, capnography module860 includes a processing component 872.

In embodiment 810, the previously mentioned monitoring circuit includesa strain gauge 870. Strain gauge 870 is attached to airway adapter 850.In addition, processing component 872 includes a resistor bridge 873.Resistor bridge 873 is made of resistors R1, R2, R3 as shown, and isconfigured to be coupled with strain gauge 870 via wires 871. Inembodiment 810, processing component 872 can be configured to generate apressure signal S879 responsive to signals on resistor bridge 873.

Strain gauges can be thus supported on various components according toembodiments. Such components can be, as seen above, a side tube, anairway adapter or coupler, an airway tube, a CPR inflow valve, and soon.

In some embodiments, a component on which the strain gauge is supportedhas proper elasticity at least at the supporting portion, for the straingauge to give good results. In some embodiments where less overallelasticity is structurally preferable otherwise, a component may includea main portion with a first elasticity and a detection portion with asecond elasticity different from the first elasticity. In suchembodiments, at least a portion of the strain gauge is coupled to thedetection portion. Usually the elasticity of the portion that supportsthe strain gauge is larger, for the strain gauge to give good results.Examples are now described.

Referring now to FIG. 9, a section of a component 901 is shown.Component 901 can be a component as described above, which in this caseis also tubular, and circular. Component 901 has a hollow interior 908,so as to accommodate an air path 949 perpendicular to the plane of thediagram. Component 901 includes a main portion 903 with a firstelasticity, and a detection portion 904 with a second elasticitydifferent from the first elasticity. At least a portion of a straingauge 907 is coupled to detection portion 904. In the example of FIG. 9,the entire strain gauge 907 is coupled to detection portion 904,although this need not be the case. An example is now described.

Referring now to FIG. 10, a section of a component 1001 is shown.Component 1001 can be a component as described above, which in this caseis also tubular, and circular. Component 1001 has a hollow interior1008, so as to accommodate an air path 1049 perpendicular to the planeof the diagram. Component 1001 includes a main portion 1003 with a firstelasticity, and a detection portion 1004 with a second elasticitydifferent from the first elasticity. At least a portion of a straingauge 1007 is coupled to detection portion 1004, while at least anotherportion of strain gauge 1007 is coupled to main portion 1003.

The different elasticities within a single component can be accomplishedin a number of ways. For example, different types of materials may beused. In some embodiments, different thicknesses are implemented, whichpermit using a singular material. Examples are now described.

Referring now to FIG. 11, a section of a component 1101 is shown.Component 1101 can be a component as described above, which in this caseis also tubular, and circular. Component 1101 has a hollow interior1108, so as to accommodate an air path 1149 perpendicular to the planeof the diagram. Component 1101 includes a main portion 1103 with a firstthickness, and a detection portion 1104 with a second thickness lessthan the first thickness. At least a portion of a strain gauge 1107 iscoupled to detection portion 1104. In other words, a section of the wallof a tube can be thinner than the ordinary tube, and embed the straingauge in that section. As such, the amount of strain resulting from apositive pressure breath may be larger in that thinner-walled area, andeasier to sense. This thinner walled section could be a longitudinalstripe in the tube, making up between 10% and 90% of the circumferenceof the tube.

In the example of FIG. 11, the entire strain gauge 1107 is coupled todetection portion 1104, although this need not be the case. An exampleis now described.

Referring now to FIG. 12, a section of a component 1201 is shown.Component 1201 can be a component as described above, which in this caseis also tubular, and circular. Component 1201 has a hollow interior1208, so as to accommodate an air path 1249 perpendicular to the planeof the diagram. Component 1201 includes a main portion 1203 with a firstthickness, and a detection portion 1204 with a second thickness lessthan the first thickness. At least a portion of a strain gauge 1207 iscoupled to detection portion 1204, while at least another portion ofstrain gauge 1207 is coupled to main portion 1203.

FIG. 13 shows a flowchart 1300 for describing methods according toembodiments. According to an operation 1310, gas may be drawn from anair path into a cuvette. The gas may be drawn by a pump.

According to another operation 1320, an amount of carbon dioxide withinthe cuvette may be detected. Detecting can be by a carbon dioxidedetector.

According to another operation 1330, a carbon dioxide signal may begenerated. Generating can be responsive to the amount of carbon dioxidedetected at operation 1320.

According to another operation 1340, a pressure in the air path may bedetected. In some embodiments, the pump is driven by a pump drivingsignal, a monitoring circuit includes a driving sensor, and the pressureis detected by the driving sensor detecting changes in the pump drivingsignal.

According to another operation 1350, a pressure signal may be generatedresponsive to the pressure in the air path detected at operation 1340.Generating may be performed by a processing component.

According to another operation 1360, the pressure signal generated atoperation 1350 may be received by a processor.

According to another operation 1370, a human-perceptible indication maybe output, responsive to the receiving at operation 1360. Outputting maybe performed by an output device.

According to another operation 1380, a record may be stored in a memoryresponsive to the receiving at operation 1360.

Embodiments further include stand-alone versions of devices describedabove, which can be disposable and inexpensive. These include versionsof a capnograph airway adapter, an impedance threshold device.Additional versions are now described.

FIG. 14 is a diagram of a sample combination device 1450 made accordingto embodiments, which combines an airway adapter with an impedancethreshold device. Device 1450 can be an impedance threshold deviceconfigured to be used together with a ventilation system, at least asdescribed above.

Device 1450 may include a tube section 1401, which has a first end 1451and a second end 1452. Tube section 1401 may be made from plastic orother suitable material. Tube section 1401 may have a hollow interior1408 for accommodating an air path 1449, when coupled between a gassource and an airway tube. Device 1450 may also include a side tube 1462coupled to tube section 1401 and communicating with hollow interior1408. Device 1450 may further include an inflow valve 1488 within tubesection 1401, and within air path 1449, and working as described above.

FIG. 15 is a diagram of a sample endotracheal (ET) system for aventilator. The ET system includes an ET tube 1540, which has two ends1541 and 1542. End 1542 is configured to be coupled to a gas source,which is not shown but can be made as described above. ET tube 1540 ishollow to define or accommodate an air path 1549 that receives bursts ofgas expelled from a gas source, when ET tube 1540 is thus coupled withthe gas source.

End 1541 is inserted in an airway of a patient 1511 having a lung 1518.Insertion is through the mouth 1514 and into trachea 1515 of patient1511. A small syringe 1544 may be used to inflate a cuff 1546 around aportion of ET tube 1546, for forming an airtight seal between theoutside of ET tube 1540 and air path 1549.

The ET system also includes a strain gauge 1570. Strain gauge 1570 iscoupled to ET tube 1540, and preferably attached to it. Strain gauge1570 can change properties when ET tube 1540 changes dimension.

The ET system further includes a bridge circuit 1573. Bridge circuit1573 can be configured to be coupled electrically with strain gauge1570, for example via conductors 1571. In some embodiments, bridgecircuit 1573 is also physically coupled with ET tube 1540, andconductors 1571 can be very short. In other embodiments, bridge circuit1573 is part of a module or a monitor, for example as described above.Bridge circuit 1573 can be used to generate a pressure signal about apressure in ET tube 1540, which can help detect spontaneous breaths asper the above.

In the methods described above, each operation can be performed as anaffirmative step of doing, or causing to happen, what is written thatcan take place. Such doing or causing to happen can be by the wholesystem or device, or just one or more components of it. It will berecognized that the methods and the operations may be implemented in anumber of ways, including using systems, devices and implementationsdescribed above. In addition, the order of operations is not constrainedto what is shown, and different orders may be possible according todifferent embodiments. Examples of such alternate orderings may includeoverlapping, interleaved, interrupted, reordered, incremental,preparatory, supplemental, simultaneous, reverse, or other variantorderings, unless context dictates otherwise. Moreover, in certainembodiments, new operations may be added, or individual operations maybe modified or deleted. The added operations can be, for example, fromwhat is mentioned while primarily describing a different system,apparatus, device or method.

A person skilled in the art will be able to practice the presentinvention in view of this description, which is to be taken as a whole.Details have been included to provide a thorough understanding. In otherinstances, well-known aspects have not been described, in order to notobscure unnecessarily this description.

This description includes one or more examples, but this fact does notlimit how the invention may be practiced. Indeed, examples, instances,versions or embodiments of the invention may be practiced according towhat is described, or yet differently, and also in conjunction withother present or future technologies. Other such embodiments includecombinations and sub-combinations of features described herein,including for example, embodiments that are equivalent to the following:providing or applying a feature in a different order than in a describedembodiment; extracting an individual feature from one embodiment andinserting such feature into another embodiment; removing one or morefeatures from an embodiment; or both removing a feature from anembodiment and adding a feature extracted from another embodiment, whileproviding the features incorporated in such combinations andsub-combinations.

In general, the present disclosure reflects preferred embodiments of theinvention. The attentive reader will note, however, that some aspects ofthe disclosed embodiments extend beyond the scope of the claims. To therespect that the disclosed embodiments indeed extend beyond the scope ofthe claims, the disclosed embodiments are to be considered supplementarybackground information and do not constitute definitions of the claimedinvention.

In this document, the phrases “constructed to” and/or “configured to”denote one or more actual states of construction and/or configurationthat is fundamentally tied to physical characteristics of the element orfeature preceding these phrases and, as such, reach well beyond merelydescribing an intended use. Any such elements or features can beimplemented in a number of ways, as will be apparent to a person skilledin the art after reviewing the present disclosure, beyond any examplesshown in this document.

Any and all parent, grandparent, great-grandparent, etc. patentapplications, whether mentioned in this document or in an ApplicationData Sheet (“ADS”) of this patent application, are hereby incorporatedby reference herein as originally disclosed, including any priorityclaims made in those applications and any material incorporated byreference, to the extent such subject matter is not inconsistentherewith.

In this description a single reference numeral may be used consistentlyto denote a single item, aspect, component, or process. Moreover, afurther effort may have been made in the drafting of this description touse similar though not identical reference numerals to denote otherversions or embodiments of an item, aspect, component or process thatare identical or at least similar or related. Where made, such a furthereffort was not required, but was nevertheless made gratuitously so as toaccelerate comprehension by the reader. Even where made in thisdocument, such a further effort might not have been made completelyconsistently for all of the versions or embodiments that are madepossible by this description. Accordingly, the description controls indefining an item, aspect, component or process, rather than itsreference numeral. Any similarity in reference numerals may be used toinfer a similarity in the text, but not to confuse aspects where thetext or other context indicates otherwise.

The claims of this document define certain combinations andsubcombinations of elements, features and steps or operations, which areregarded as novel and non-obvious. Additional claims for other suchcombinations and subcombinations may be presented in this or a relateddocument. These claims are intended to encompass within their scope allchanges and modifications that are within the true spirit and scope ofthe subject matter described herein. The terms used herein, including inthe claims, are generally intended as “open” terms. For example, theterm “including” should be interpreted as “including but not limitedto,” the term “having” should be interpreted as “having at least,” etc.If a specific number is ascribed to a claim recitation, this number is aminimum but not a maximum unless stated otherwise. For example, where aclaim recites “a” component or “an” item, it means that it can have oneor more of this component or item.

1. (canceled)
 2. A capnograph system configured to be used together with a ventilation system, the ventilation system including a gas source configured to expel repeated bursts of gas and an airway tube defining an air path that communicates with the gas source, the airway tube configured to be inserted in an airway of a patient so as to guide the bursts of gas as artificial inhalations to a lung of the patient, the capnograph system comprising: a capnography module including: a cuvette configured to communicate with the air path, and a pump configured to draw gas from the air path into the cuvette, the pump configured to receive a driving signal and operate responsive to the driving signal; and a monitoring circuit including a driving sensor configured to detect changes in the driving signal; and a processor configured to detect spontaneous breaths of the patient based at least in part on changes in the driving signal.
 3. The capnography system of claim 2, wherein the driving sensor is configured to detect a voltage at a power node of the pump to detect changes in the driving signal.
 4. The capnography system of claim 2, wherein the driving sensor is configured to detect a current of a conductor attached to the pump to detect changes in the driving signal.
 5. The capnography system of claim 2, wherein the processor is configured to detect spontaneous breaths of the patient based at least in part on changes in the driving signal by detecting an increase in driving signal to indicate a spontaneous breath.
 6. The capnography system of claim 2, wherein the capnography module further includes a carbon dioxide detector configured to detect a concentration of carbon dioxide within the air path and to generate a carbon dioxide signal responsive to the detected concentration of carbon dioxide in exhalations of the patient.
 7. The capnography system of claim 6, wherein the processor is further configured to detect spontaneous breaths of the patient based at least in part on the carbon dioxide signal.
 8. The capnography system of claim 7, wherein the processor is configured to combine the carbon dioxide signal and the driving signal into a combined signal and to detect spontaneous breaths of the patient based at least in part on the combined signal.
 9. The capnography system of claim 8, wherein the processor is further configured to combine the carbon dioxide signal and the driving signal into the combined signal by removing peaks in the carbon dioxide signal that correspond to peaks in the driving signal.
 10. The capnograph system of claim 2, wherein the monitoring circuit is wholly included within the capnography module.
 11. The capnograph system of claim 2, further comprising an output device configured to output a human-perceptible indication responsive to the processor receiving the driving signal.
 12. The capnograph system of claim 11, further comprising a monitor that includes the capnography module, the processor and the output device.
 13. The capnograph system of claim 11, further comprising a defibrillator.
 14. A method for a capnograph system that is configured to be used together with a ventilation system, the ventilation system including a gas source expelling repeated bursts of gas and an airway tube defining an air path that communicates with the gas source, the airway tube inserted in an airway of a patient and guiding the bursts of gas as artificial inhalations to a lung of the patient, the method comprising: drawing, by a pump, gas from the air path into a cuvette in a capnography module at a constant rate based on a pump driving signal; detecting changes in the pump driving signal by a driving sensor; generating, by a processing component, a pressure signal responsive to the detected changes in the pump driving signal; and detecting a spontaneous breath of the patient based at least in part on the pressure signal.
 15. The method of claim 14, wherein detecting the pressure includes detecting a voltage at a power node of the pump to detect changes in the driving signal.
 16. The method of claim 14, wherein detecting the pressure includes detecting a current of a conductor attached to the pump to detect changes in the driving signal.
 17. The method of claim 14, wherein detecting the spontaneous breaths of the patient based at least in part on the pressure signal includes detecting an increase in driving signal to indicate a spontaneous breath.
 18. The method of claim 14, further comprising detecting a concentration of carbon dioxide within the air path and generating a carbon dioxide signal responsive to the detected concentration of carbon dioxide in exhalations of the patient.
 19. The method of claim 18, wherein detecting spontaneous breaths of the patient is based at least in part on the carbon dioxide signal.
 20. The method of claim 19, further comprising combining the carbon dioxide signal and the pressure signal into a combined signal and detecting the spontaneous breaths of the patient based at least in part on the combined signal.
 21. The method of claim 20, wherein combining the carbon dioxide signal and the driving signal into the combined signal includes removing peaks in the carbon dioxide signal that correspond to peaks in the pressure signal. 